EP3824954A1 - Vorrichtung, einrichtung und verfahren zur ministrahl-strahlentherapie - Google Patents

Vorrichtung, einrichtung und verfahren zur ministrahl-strahlentherapie Download PDF

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Publication number
EP3824954A1
EP3824954A1 EP19306515.8A EP19306515A EP3824954A1 EP 3824954 A1 EP3824954 A1 EP 3824954A1 EP 19306515 A EP19306515 A EP 19306515A EP 3824954 A1 EP3824954 A1 EP 3824954A1
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EP
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Prior art keywords
quadrupole
equal
less
incident beam
minibeam
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EP19306515.8A
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English (en)
French (fr)
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designation of the inventor has not yet been filed The
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Centre National de la Recherche Scientifique CNRS
Institut Curie
Universite Paris Saclay
Original Assignee
Centre National de la Recherche Scientifique CNRS
Institut Curie
Universite Paris Saclay
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Application filed by Centre National de la Recherche Scientifique CNRS, Institut Curie, Universite Paris Saclay filed Critical Centre National de la Recherche Scientifique CNRS
Priority to EP19306515.8A priority Critical patent/EP3824954A1/de
Priority to US17/755,581 priority patent/US20220362580A1/en
Priority to EP20815731.3A priority patent/EP4061483A1/de
Priority to PCT/EP2020/082766 priority patent/WO2021099511A1/en
Priority to JP2022529793A priority patent/JP2023502731A/ja
Publication of EP3824954A1 publication Critical patent/EP3824954A1/de
Pending legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1042—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1042—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head
    • A61N5/1043—Scanning the radiation beam, e.g. spot scanning or raster scanning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B18/26—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor for producing a shock wave, e.g. laser lithotripsy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1077—Beam delivery systems
    • A61N5/1078—Fixed beam systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
    • A61N2005/1087—Ions; Protons

Definitions

  • the present invention concerns a method, a device and an apparatus to provide charged particle minibeam radiation therapy.
  • the present invention relates, in particular, to a scanning nozzle and a method to generate a proton minibeam for proton minibeam radiation therapy (pMBRT).
  • pMBRT proton minibeam radiation therapy
  • output proton beams of a medical facility beamline as for instance an output proton beam of a pencil beam scanning (PBS) nozzle
  • PBS pencil beam scanning
  • FWHM full width at half maximum
  • pMBRT techniques carried out at clinical centers, known in the state of the art consist in emitting a proton beam from a proton beam source towards a target and arranging a collimator at a predefined distance from the target to generate an array of areas of high dose values, called peaks, adjacent to areas of low dose values, called valleys.
  • Such minibeams significantly increase dose tolerances and sparing of normal tissue.
  • These collimators called multislit collimators, consist of an array of slices and slits, one slice being arranged between two slits.
  • Such pMBRT devices are arranged to shape the proton beam and consist of a proton beam source, a nozzle and a collimator. The current nozzles are voluminous with rather long propagation distances of the beam, such that minibeam generation at clinical centers is only possible using collimators.
  • Another major drawback of using collimators lies in the significant production of harmful secondaries, or harmful side effects, close to the patient due to the proton beam being scattered by the collimator.
  • the harmful secondaries are produced in direct vicinity of the patient and at level of the therapists while manipulating the collimator after the treatment.
  • An object of the invention is to provide a minibeam scanning nozzle and a method to generate charged particle minibeams.
  • a method to generate a minibeam comprising the steps consisting of:
  • the fourth direction is orthogonal to the third direction.
  • the minibeam may be generated from an incident beam of charged particles that exhibits:
  • the minibeam generated through the method according to the invention is intended to be used for minibeam radiation therapy.
  • the term adjust may be understood as set.
  • the magnetic field gradients may be determined, set or adjusted based on the parameters of the incident beam, for instance the energy and/or the divergence and/or the size and/or an absolute value of a correlation coefficient between a size of the incident beam and the divergence of the incident beam.
  • the minibeam may be generated from an incident beam of charged particles that exhibits:
  • the minibeam may be generated from an incident beam of charged particles that exhibits:
  • the energy of a particle of the incident beam of charged particles is less than 1000 MeV/nucleon.
  • the energy of a particle of the incident beam of charged particles is comprised between 50 and 250 MeV, preferably between 100 and 230 MeV
  • the size of the incident beam may be defined as a diameter of the incident beam. If the incident beam is considered as a Gaussian beam, the size of the beam may be defined through a couple consisting of a vertical full width at half maximum (vFWHM) and a horizontal FWHM (hFWHM).
  • vFWHM vertical full width at half maximum
  • hFWHM horizontal FWHM
  • a focal length of the second quadrupole, or respectively of the first quadrupole may be defined as the distance between the second quadrupole, or respectively the first quadrupole, and a focal point of the second quadrupole, or respectively of the first quadrupole.
  • a distance between a focal point of the first quadrupole and a focal point of the second quadrupole may be less than or equal to 50 cm in order for the focused beam to meet the criteria of a minibeam along the volume extending between the focal point of the first quadrupole and the focal point of the second quadrupole.
  • the focal length of the first quadrupole and/or the focal length of the second quadrupole is superior or equal to 60 cm, more preferably superior or equal to 70 cm, even more preferably superior or equal to 80 cm and in a preferred manner superior or equal to 90 cm.
  • the focal length of the second quadrupole is less than or equal to 180 cm, more preferably less than or equal to 160 cm, even more preferably less than or equal to 150 cm, in a preferred manner less than or equal to 140 cm, in a more preferred manner less than or equal to 130 cm and in a particularly preferred manner less than or equal to 120 cm.
  • the focal length of the first quadrupole is less than or equal to 220 cm, more preferably less than or equal to 200 cm, even more preferably less than or equal to 180 cm, in a preferred manner less than or equal to 160 cm, in a more preferred manner less than or equal to 140 cm, in a particularly preferred manner less than or equal to 130 cm.
  • the adjustment of the magnetic field gradient generated by the second quadrupole and/or of the magnetic field gradient generated by the first quadrupole may be defined as controlling the magnetic field gradients generated by the second quadrupole and/or by the first quadrupole so that the vFWHM and hFWHM of the focused beam meet the criteria of a minibeam.
  • the vFWHM and hFWHM of the focused beam meet the criteria of a minibeam in the volume extending between the focal point of the first quadrupole and the focal point of the second quadrupole.
  • the incident beam may be deflected through the third and fourth magnets so as to move a point of intersection between the charged particle minibeam and a target.
  • the first and second quadrupoles and the third and fourth magnets may be part of a nozzle.
  • the nozzle may be a scanning nozzle.
  • the nozzle may be a scanning nozzle according to the invention.
  • the focused beam is focused and deflected downstream of the exit of the scanning nozzle, according to a beam path.
  • the method may comprise the step consisting of arranging the beam, the first and second quadrupoles and the third and fourth magnets in a volume, where the beam is contained in a vacuum environment, said vacuum environment extending over a distance higher than 50 cm and lower than 200 cm.
  • the magnets are not in the vacuum chamber, only the beam.
  • the vacuum chamber or tube passes through the magnets. It is however possible to design a system where all components are in a vacuum environment, but only an ionization chamber can be in an air filled environment.
  • the vacuum environment may be generated inside a vacuum chamber.
  • the vacuum chamber may be a vacuum chamber of a scanning nozzle.
  • a distance from an end of the vacuum environment to the focal point of the second quadrupole may be superior to few centimeters and/or is less than or equal to 50 cm.
  • a distance from an end of the vacuum environment to the focal point of the second quadrupole may be superior or equal to 10 cm.
  • a distance from an end of the vacuum environment to the focal point of the second quadrupole may less than or equal to 40 cm, more preferably less than or equal to 30 cm.
  • the end of the vacuum environment may be an edge of the vacuum environment and/or an end of the vacuum chamber and/or an edge of the vacuum chamber.
  • a FWHM of the incident beam may be less than 50 mm.
  • Values of magnetic field gradients generated by the first and second quadrupoles, required so that the beam focused at the focal point of the second quadrupole meets the criteria of a minibeam, may be superior or equal to 0 and/or are less than or equal to 1.6 T.cm -1 .
  • a distance separating the first quadrupole from the second quadrupole may be less than 15 cm, preferably less than 6 cm, more preferably less than or equal to 3 cm.
  • the incident beam of charged particles may exit from a beamline of a medical facility.
  • the incident beam of charged particles may be an output beam of a beamline of a medical facility
  • the charged particles may be ions.
  • the charged particles are protons or carbon ions.
  • Operational frequencies of the third and fourth magnets may be superior or equal to 1 Hz and/or are less than or equal to 200 Hz.
  • a minibeam is defined as the maximum size of a beam under which the desired tissue sparing effect takes place.
  • This maximum beam size is defined as being a full width at half maximum (FWHM) value of the beam equal to 2 mm at an entrance plane of a target to be irradiated.
  • FWHM full width at half maximum
  • this maximum beam size may also be defined as being equal to 2.355 ⁇ of the beam Gaussian distribution, where ⁇ is the standard deviation.
  • the entrance plane of a target to be irradiated may be located in the volume extending between the focal point of the first quadrupole and the focal point of the second quadrupole.
  • the minibeam is defined as a beam that exhibits a FWHM less than or equal to 2 mm.
  • a minibeam according to the invention may exhibit a horizontal full width at half maximum (hFWHM) less than or equal to 2 mm and a vertical FWHM (vFWHM) equal to or less than the hFWHM of the minibeam.
  • hFWHM horizontal full width at half maximum
  • vFWHM vertical FWHM
  • a minibeam according to the invention may exhibit a FWHM less than or equal to 2 mm.
  • a minibeam exhibits a FWHM, at the volume extending between the focal point of the first quadrupole and the focal point of the second quadrupole, less than or equal to 1 mm, more preferably less than or equal to 0.9 mm, in a preferred manner less than or equal to 0.8 mm and in a more preferred manner less than or equal to 0.7 mm.
  • the method may comprise the step consisting of measuring the intensity and/or the spatial location of the focused beam downstream of the first and second quadrupoles and the third and fourth magnets according to the beam path.
  • the method may comprise the step consisting of measuring the intensity and/or the spatial location of the focused beam at a position located between the fourth magnet and the focal point of the first quadrupole.
  • a minibeam scanning nozzle for charged particle minibeam radiation therapy, said MSN comprising, along a beam path of the charged particles inside the nozzle:
  • the MSN may comprise a vacuum chamber wherein the beam is contained passing through the first and second quadrupoles and the third and fourth magnets.
  • the vacuum chamber is preferably arranged in the bore of the magnets.
  • a distance between an exit face of the vacuum chamber and the focal point of the second quadrupole may be less than 50 cm.
  • the MSN may be arranged to generate the minibeam from an incident beam of charged particles exiting a beamline of a medical facility, the MSN being intended to be arranged downstream of the beamline in a path of the incident beam of charged particles.
  • the third and/or the fourth magnets may be scanning dipole magnets.
  • the first quadrupole and/or the second quadrupole and/or the third magnet and/or the fourth magnet are superconducting magnets.
  • the first and/or the second quadrupoles are arranged to generate magnetic field gradient superior or equal to 0 and/or less than or equal to 1.6 T.cm -1 .
  • the first, second, third and/or fourth magnets are part of a multipole magnet.
  • the multipole magnet may comprise eight or more poles.
  • the first, second, third and/or fourth magnets are part of an octupole magnet.
  • the third and/or the fourth magnets may be arranged to deflect the beam propagating within the vacuum chamber so as to move a point of intersection between the charged particles minibeam and the target.
  • the scanning nozzle may comprise one or more ionization chambers.
  • a gaseous material filling the ionization chambers is an inert gas or a noble gas.
  • the gaseous material filling the ionization chambers is air or helium or a gas mixture.
  • the MSN according to the invention may be arranged to carry out the method according to the invention.
  • the MSN may be used for irradiating a tumor.
  • the MSN may be used for the treatment of a tumor located in a patient.
  • the MSN may be used for the treatment of cancer.
  • a system for charged particles minibeam radiation therapy comprising:
  • the system for charged particles minibeam radiation therapy may comprise a beam source arranged to generate an incident beam of charged particles that exhibits:
  • the beam source may comprise a beamline of a medical facility.
  • the MSN of the system for charged particles minibeam radiation therapy may be the MSN according to the invention.
  • a selection may comprise features isolated from a set of features (even if this selection is isolated among a sentence comprising other features thereof), if the selection is sufficient to confer a technical advantage or to distinguish the invention form the state of the art.
  • This selection comprises at least a feature, preferably described by its technical function without structural features, or with a part of structural details if this part is sufficient to confer a technical advantage or to distinguish the invention form the state of the art on its own.
  • Usual pMBRT system comprises a beam source.
  • the beam source comprises a proton accelerator, such as a cyclotron, and a beam transport system comprising magnets and being arranged to convey an incident proton beam 6 from the proton accelerator to the nozzle 2.
  • protons may be substituted with other ions, such as carbon ions.
  • the beam is finally shaped with a collimator to generate an array of areas of high dose values and/or is deflected to generate a scanning beam.
  • An embodiment according to the invention comprises a proton minibeam radiation therapy (pMBRT) system (not represented).
  • the system comprises a nozzle 2 according to the invention.
  • the nozzle 2 according to the invention is arranged to shape the incident proton beam 6 into a proton minibeam 16 and to guide said proton minibeam 16 towards a tumor (not depicted) located in a patient 7.
  • the patient is located in a gantry which is part of the pMBRT system.
  • the nozzle 2 is connected to the gantry (not represented) and the gantry is arranged to rotate the nozzle 2 around the patient 7 so as to enable treatment with multiple fields from different angles to better target the tumor and spare surrounding healthy tissue.
  • Typical ⁇ values of current proton beams 6 used in current facilities are between 2 and 10 mm.
  • Standard energy values of current proton beams 6 used in current facilities are between 60 and 230 MeV.
  • a standard divergence exhibited by current proton beams 6 is around 3 mrad (milliradians).
  • FIGURE 1 shows an embodiment of the nozzle 2 arrangement according to the invention that has been found suitable for minibeam generation compared to numerous different potential nozzle arrangements investigated (see below) that are not suitable.
  • the nozzle 2 comprises a vacuum chamber 9 arranged to receive the incident proton beam 6. Coming from the transport system, the proton beam propagates into the vacuum chamber 9. According to the beam path, in other words from left to right of the figure 1 , the nozzle 2 comprises:
  • the nozzle 2 also comprises an ionization chamber 14.
  • the vacuum chamber 9 extends from an entrance face 32 of the nozzle 2, through which the proton beam 6 enters the vacuum chamber 9, to an exit of the dipole 13, through which the proton minibeam 16 exits the vacuum chamber 9 towards the target 7 (which can be a tumor for example) through an ionization chamber 14.
  • the quadrupoles 10, 11, the dipoles 12, 13 are out of the vacuum environment of the vacuum chamber 9.
  • the proton beam propagates in the vacuum chamber through each quadrupole 10, 11, then between the two poles of each scanning dipole 12, 13 and is located at equal distance from each pole of a scanning dipole 12, 13. Then, the proton minibeam 16 passes through the ionization chamber 14 before exiting the vacuum chamber and propagating towards the target 7.
  • the first quadrupole 10 is arranged to focus the proton beam 6 propagating within the vacuum chamber 9 according to the y direction and the second quadrupole 11 is arranged to focus the proton beam 6 propagating within the vacuum chamber 9 according to the x direction.
  • Each of the first 10 and the second quadrupoles 11 is arranged to provide a variable magnetic field gradient. Downstream of the second quadrupole 11, according to the beam path, the proton beam is focused to meet the criteria of a minibeam along a volume extending between a focal point of the first quadrupole 10 and a focal point of the second quadrupole 11.
  • the ionization chamber 14 is arranged to measure the intensity and the size and position of the proton minibeam 16.
  • the wall parts of each ionization chamber located on the beam path may be made of mylar.
  • the ionization chamber 14 is filled with air or helium.
  • the first scanning dipole 12 is arranged to deflect the proton beam propagating within the vacuum chamber 9 according to the y direction and the second scanning dipole 13 is arranged to deflect the proton beam 6 propagating within the vacuum chamber 9 according to the x direction.
  • Each of the first 12 and the second scanning dipole 13 is arranged to provide an approximatively homogeneous magnetic field of variable strength.
  • a processing unit for use in connection with the nozzle 2, is arranged to control the magnetic field gradient value provided by each of the first 12 and the second scanning dipole 13 so as to deflect the proton beam 6 propagating within the vacuum chamber 9 so as to move the point of intersection between the proton minibeam 16 and a given section plane 18 of the target 7.
  • the pattern 17 exhibits a crenellated shape.
  • the pattern may also be any type of alternating array of areas of high dose values, called peaks and areas of low dose values, called valleys. As non-limiting examples, the areas may be circles or ellipses or squares or rectangles and may be concentric.
  • Each of the first 12 and the second 13 scanning dipole exhibits an operational frequency between 1 and 200 Hz. An operational frequency range of 3 to 100 Hz is suitable in most cases. Downstream of the second scanning dipole 13, according to the beam path, the proton beam 16 is focused and deflected.
  • Embodiments on figures 2a, 2c and 2d illustrate a chamber 2 containing a vacuum chamber 9 conveying the beam.
  • the vacuum chamber passes through the components 10-13.
  • the magnets are disposed around the vacuum chamber, not inside. Others components are in an air filled volume.
  • the whole chamber 2 is in a vacuum environment, thus it is considered as the vacuum chamber 9.
  • the ionization chamber 14 is always arranged in an air filled volume.
  • FIGURE 2a illustrates a setup currently used in medical facilities for radiation therapy.
  • the current setup comprises a snout 23 arranged to receive a collimator and to obtain a shaped proton beam 24 from the focused beam 16, which is not a minibeam, prior to impact the target 7.
  • the snout 23 is in the ambient air and is mounted on a snout holder 25.
  • a ionization chamber 14 is placed downstream of the vacuum chamber 9.
  • the current setup comprises a vacuum window 28 arranged in the ambient air upstream a vacuum chamber 9.
  • a first 10 and a second 11 quadrupole and a first 12 and a second 13 scanning magnet are arranged out of the vacuum chamber 9.
  • Figure 3 shows four bar charts depicting the minimum sizes of the focused beam 16, calculated from the simulations, achieved by the setup arrangements of Figures 2a, 2b, 2c and 2d from left to right.
  • the bar charts of Figures 3a, 3b and 3d related to arrangements of Figures 2a, 2b and 2d show the horizontal FWHM (hFWHM) and the vertical FWHM (vFWHM) of the shaped proton beam 24 at the target 7 for an energy of the incident proton beam 6 of 100 and 200 MeV
  • the chart of the Figure 3c related to the arrangement of Figure 2c shows the horizontal FWHM (hFWHM) and the vertical FWHM (vFWHM) of the focused beam 16 at the target 7 for energy of the incident proton beam 6 of 100 and 200 MeV.
  • the beam 16 produced by the nozzle 2 according to the invention meets the criteria of a minibeam at a target 7 and may be used for pMBRT.
  • the nozzle 2 according to the invention is considered.
  • the precise dimensions of the nozzle 2 and the features of the nozzle 2 components, the distances separating the components of the nozzle 2 between each other and the components of the nozzle 2 from the target 7 have been simulated with an analytical calculation code for magnetic fields and checked through Monte Carlo method using TOPAS code version 3.2 and 3.1.
  • the components comprise the first 10 and the second 11 quadrupoles, the third 12 and the fourth 13 scanning dipoles and the ionization chamber 14.
  • each component of the nozzle 2 The size of each component of the nozzle 2, the distances separating these components from one another and the distances separating these components from the target 7 are introduced.
  • Each component length presented hereinafter describes the size of a component along the beam path.
  • the size of each component is defined by the distance separating an entrance plane and an exit plane of a component.
  • the distance d2 separating the exit face of the second quadrupoles 11 from the section plane 18 of the target 7.
  • the distance d2 should be less than 200 cm.
  • a distance d2 less than 200 cm is only achievable by means of the nozzle 2 arrangement according to the invention and also because the nozzle 2 according to the invention does not use a snout 23 or a physical collimator. Indeed, the distance d2 in current setups used in medical facilities, as shown Figure 2a , is generally superior to 230 cm.
  • this distance d5 is less than 50 cm.
  • a distance d5 is achievable because the nozzle 2 according to the invention does not use a snout 23 or a physical collimator.
  • the minibeams and in particular the minibeams generated from medical facilities, are considered to be achievable only by using a collimator mounted on the snout 23 and/or a collimator. Therefore, removing the snout 23 and/or the collimator has been counterintuitive.
  • the distance between the entrance plane 32 of the nozzle 2 and the entrance face of the first quadrupole 10, the first quadrupoles 10 length (lq1) and the second quadrupoles 11 length (lq2), the distance d1 separating the first quadrupoles 10 and the second quadrupoles 11, the first scanning dipole 12 length (ld1), the second scanning dipole 13 length (ld2), the distance between the exit face of the second quadrupole 11 and the entrance face of the first scanning dipole 12 (d6), the distance between the exit face of the first scanning dipole 12 and the entrance face of the second scanning dipole 13 (d4), the distance between the exit face of the second scanning dipole 13 and the entrance face of the ionization chamber 14 (d7), the ionization chamber 14 length (li1), the distance between the exit face of the ionization chamber 14 and the exit plane 33 of the nozzle 2 and the distance d5 between the exit plane 33 of the nozzle 2 and the section plane 18 of the tumor are
  • a quadrupole 10, 11 usually has a cylindrical shape. From the calculation, the diameter of this assembly is 20 cm in the present embodiment; the diameter being orthogonal to the beam path. A height and a width of the dipoles 12, 13 and the ionization chamber 9 are 20 cm. A diameter of the vacuum chamber 9 is about 5 cm. A vacuum is maintained within the nozzle 2.
  • the distance lq1 is equal to lq2 is less than 20 cm, preferably comprised between 3 and 20 cm, more preferably comprised between 5 and 15 cm and is equal to 10 cm in the present embodiment.
  • the distance d1 is less than 15 cm, preferably less than 6 cm and is equal to 3 cm in the present embodiment.
  • the distance li1 is less than 30 cm, preferably comprised between 2 and 15 cm, and is equal to 10 cm in the present embodiment.
  • the distance d2 is less than 200 cm, and preferably between 90 and 110 cm in the present embodiment.
  • the distance (d3) between the beam entrance face 32 the nozzle 2 and the section plane 18 of the tumor is less than 260 cm, generally comprised between 130 and 160 cm and preferably between 130 and 150 cm in the present embodiment.
  • the distance ld1 is equal to ld2 is less than 40 cm and is equal to 25 cm in the present embodiment.
  • the distance d4 is less than 10 cm and is equal to 0 cm in the present embodiment.
  • the distance d6 is less than 15 cm and is equal to 5 cm in the present embodiment.
  • the distance d7 is less than 30 cm and is equal 15 cm in the present embodiment.
  • the nozzle 2 according to the invention avoids the use of collimators.
  • the use of collimators in current pMBRT devices causes the loss of a major part of the total flux of the proton beam 6. Thus, the dose rate is strongly lowered.
  • the nozzle 2 according to the invention allows transmitting the total flux of the proton beam 6 to the tumor. Thus, the dose rate is significantly increased compared to current pMBRT. Moreover, avoiding the use of a collimator allows to significantly decrease the production of harmful secondaries close to the patient.
  • the magnetic field gradient generated by the first 10 and/or the second 11 quadrupoles are adjusted, by the processing unit, so that the focal length of the first 10 quadrupole is superior or equal to 60 and/or is less than or equal to 250 cm and/or the focal length of the second 11 quadrupole is superior or equal to 50 and/or is less than or equal to 240 cm.
  • the magnetic field gradients generated by the quadrupoles 10, 11 are adjusted so that:
  • the inventors showed that the focusing capabilities of the nozzles strongly depend on parameters of the incident beam 6.
  • the inventors observed that at least one among the divergence of the incident beam 6 and the correlation coefficient between the size of the incident beam 6 and the divergence of the incident beam 6 has to be controlled.
  • the size of the incident beam 6 has a negligible effect.
  • the divergence of the incident beam 6, the absolute value of the correlation coefficient between a size of the incident beam 6 and the divergence of the incident beam 6, the energy of the incident beam 6 and the arrangement of the medical facility will vary.
  • the magnetic field gradient generated by the first 10 and/or the second 11 quadrupole are adjusted, through the processing unit, so that the focal length of the second 11 quadrupole is superior or equal to 50 and/or is less than or equal to 240 cm in order for the focused beam 16 to meet the criteria of a minibeam at the focal point of the second 11 quadrupole.
  • the focal point of the first quadrupole 10 and the focal point of the second 11 quadrupole are arranged so that the target 7, or a section plane 18 of the target 7 or an entrance plane 18 of the target 7, is located within the volume extending between the focal point of the first quadrupole 10 and a focal point of the second 11 quadrupole.
  • the nozzle 2 according to the invention is suitable is suitable to be used in every medical facility only by adjusting the magnetic field gradients of the first 10 and/or of the second 11 quadrupoles.

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EP19306515.8A 2019-11-22 2019-11-22 Vorrichtung, einrichtung und verfahren zur ministrahl-strahlentherapie Pending EP3824954A1 (de)

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EP19306515.8A EP3824954A1 (de) 2019-11-22 2019-11-22 Vorrichtung, einrichtung und verfahren zur ministrahl-strahlentherapie
US17/755,581 US20220362580A1 (en) 2019-11-22 2020-11-19 Device, apparatus and method for minibeam radiation therapy
EP20815731.3A EP4061483A1 (de) 2019-11-22 2020-11-19 Vorrichtung, einrichtung und verfahren zur ministrahl-strahlentherapie
PCT/EP2020/082766 WO2021099511A1 (en) 2019-11-22 2020-11-19 Device, apparatus and method for minibeam radiation therapy
JP2022529793A JP2023502731A (ja) 2019-11-22 2020-11-19 ミニビーム放射線療法のためのデバイス、装置、及び方法

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EP20815731.3A Pending EP4061483A1 (de) 2019-11-22 2020-11-19 Vorrichtung, einrichtung und verfahren zur ministrahl-strahlentherapie

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US20100187446A1 (en) * 2009-01-23 2010-07-29 Dilmanian F Avraham Heavy Ion Therapy with Microbeams

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US20220362580A1 (en) 2022-11-17
JP2023502731A (ja) 2023-01-25
WO2021099511A1 (en) 2021-05-27
EP4061483A1 (de) 2022-09-28

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